Fasteners having coordinated self-seeking conforming members and uses thereof

ABSTRACT

Fasteners having coordinated self-seeking conforming members for implanting into a cavity such as a hole, tube, or hard tissue defect are provided. An actuator mechanism translates applied force to conform members of a plurality of members to the cavity. The fasteners may be used for implanting a prosthetic device into hard tissue of humans or animals, for anchoring a device while the device is being worked on, or for centering a device in a hole or tube, such as in well technology. The mechanism operates expanding members so that they independently or dependently conform and apply a controlled and known pressure to surrounding materials.

This application is a continuation application of U.S. Ser. No.08/797,591 filed Feb. 7, 1997 now U. S. Pat. No. 5,882,351, which is acontinuation application of then copending PCT/US96/15722 filed Sep. 27,1996 which claims priority to U.S. Ser. No. 60/042,914 filed Sep. 29,1995. These applications are incorporated by reference herein.

FIELD OF THE INVENTION

The present invention relates to fasteners having coordinatedself-seeking conforming members and uses thereof. The fasteners may beused for anchoring a prosthesis, or for centering or aligning astructure within a hole, tube, or cavity. In particular, hard tissueimplant fasteners are envisioned for attaching a prosthesis to bone orcartilage. Methods of using said fasteners are also provided.

BACKGROUND OF THE INVENTION

Prior art references relate to structures adapted to expand the radialprojection of the device after the device has been inserted into acavity. Three groups of prior art are outlined by structuralsimilarities in their expansion characteristics. A fourth group relatesto other expansion characteristics.

Axial contraction is used to produce radial expansion once a device hasbeen inserted into a cavity. Wigam (U.S. Pat. No. 3,505,921) and Talan(U.S. Pat. No. 4,309,136) disclose construction fastening devices.Fischer et al. (U.S. Pat. No. 3,779,239) and Rublenik (SU 1,386,182-A)relate to elongated fasteners that employ radial expansion elements atthe distal end of the device. These fasteners are intended to securefractured portions of bone tissue. Kuslich (U.S. Pat. No. 5,059,193)relates to a spinal implant for use between vertebrae. Tansey (U.S. Pat.No. No. 4,681,590) relates to a structure having metal strips securedbetween an upper plate and a nut. The nut is mounted on a screw andconstrained against rotation so that rotating the screw reduces theaxial separation of the nut and upper plate causing the metal strips toexpand radially. Tansey also relates to a femoral stem prosthesis.

Oblique contact has been used between moving elements to expand theradial projection of devices that have been inserted into a cavity. Onecommon example of this type of fastener is from Aginsky (U.S. Pat. No.4,091,806). In this mechanism, a central shaft is displaced relative toan outer concentric shaft. The central shaft includes a wedge thatobliquely contacts a longitudinally slotted portion of the outerconcentric shaft. The oblique contact translates the axial force on thewedge into a radial force that expands the outer concentric shaftradially. Prior art having multiple elements actuate the elements suchthat the elements cannot be expanded independently to adapt to thecontours of the cavity in which they are placed.

Pivotal connections have been used to expand the radial projection ofdevices once they are inserted into a cavity. Prior art relates toelements pivotally connected to the device that are contacted by anaxially displaceable element. The axial force at a distance from thepivotal connection creates a torque that rotates the pivotally connectedelements into a new position that has a greater radial diameter. Some ofthese references disclose mechanisms that also use oblique contact toprovide the necessary torque. As examples of this type of mechanism, seeAvila (U.S. Pat. No. 3,986,504), Davis (U.S. Pat. No. 5,057,103),Dobelle (U.S. Pat. Nos. 2,685,877 and 3,024,785), and Firer (SU1,524,880A). None of the references in this group relate to means forcoordinated self-seeking conforming of elements. Aginsky (U.S. Pat. Nos.4,204,531 and 4,227,518) relate to use of pivotal connections in adifferent structure. A pivot point is movably mounted in a longitudinalslot. The pivot point is pivotally coupled to two legs that arepivotally coupled at their other ends to two sections of the outersheath. When the outer sheath is displaced axially, the pivot point isconstrained by the slot and the sections of the outer sheath are rotatedradially by the legs. This structure does not allow coordinatedself-seeking conforming actuation of the two outer sheath sections.

Bolesky (U.S. Pat. No. 4,275,717) and Street (U.S. Pat. No. 3,216,414)relate to elements that are biased to expand radially. These elementsare elastically constrained by a ring or cap that is axially displacedonce the device is inserted so that the biased elements can resume aradially expansive position. Erlich-DeGuemp (FR 2,387,638) relates to adevice that uses the bone tissue surface to provide an oblique contactfor radial expansion. Mühlbayer (DT 1,075,793) relates to use of arotating central shaft to translate a band which has three pinnedelements that are allowed to rotate radially. The pinned elements canrotate freely but are not driven by a mechanism and do not provide ameans to engage the three rotating elements in a coordinatedself-seeking conforming manner.

A review of the product literature shows adaptations of mechanismsimilar to Livingston (U.S. Pat. Nos. 2,699,774 and 2,490,364), Fisher(U.S. Pat. No. 3,805,775) and Flander (U.S. Pat. No. 3,708,883). An AltaModular Trauma System product (Howmedica, Rutherford, N.J.) uses aslotted sleeve, wedge shaped inner mandrel and translation of themandrel in the sleeve to increase radial diameter. Other companies aregenerally introducing unicortical fasteners (engages only one bonycortex) consisting of a slotted externally threaded hollow cylinder witha threaded inner mandrel that when rotated expands the radial diameterof the outer cylinder. One example of this type of device is the SargonImplant system (Sargon Enterprises, Inc., Beverly Hills, Calif.).

Bone implants have been used to solve health care problems of orthopedicand maxillofacial reconstruction, prosthesis fixation, drug delivery andfracture stabilization. Heretofore, bone and cartilage (hard tissue)implants were fastened with screw threads, interference fits, uniformlyexpanding mechanisms and cement. The majority of these devices andassociated techniques provide poor initial fixation, and following boneformation around the device, provide good fixation but often for only alimited period of time. Implant removals are frequently performedfollowing failure of the bone-implant interface and clinical looseningof the device.

The principal cause for implant failure in hard tissue is the separationof bone from the surface of the implant. Bone resorption about animplant is induced by micromotion of the device relative to thesurrounding hard tissue, adverse tissue reaction to the implantmaterial, or tissue necrosis due to drill heating and mechanical stressconcentrations. Micromotion is often due to poor initial stabilizationof a threaded, interference fit or cemented device.

Bone and cartilage are tissues with viscoelastic material properties.Their modulus of elasticity and ultimate strength are much less than themetal and ceramic materials used for hard tissue implants. This mismatchin material properties is a factor in device-tissue interfacialmicromotion, interface stress concentration and implant loosening. Thisproblem is compounded by bone's range of morphology and materialproperties.

The bone organ contains two distinct types of bone tissue. Cortical boneis the hard structural bone that forms the outer shell of the skeleton.Cancellous bone is contained within cortical bone and makes up asignificant portion of the volume of most bones. Cancellous bone isporous, trabecular in structure, highly vascular, filled with cellularelements and undergoes active remodeling (formation and resorption).

Heretofore bone implants placed transverse to the long axis of bonepenetrated a short segment of the cortical bone shell and had asignificant portion of their surface adjacent to cancerous bone. Thesedevices relied on both the cortical and cancerous bone for initial andlong-term stability. Implant dependence on porous low strengthcancellous bone and limited cortical bone contact causes poor devicestability.

Heretofore bone implants that were placed along the long central axis ofbone were designed to occupy much of the cancerous bone space andcontact the endosteal surface (inner surface) of cortical bone. Theirregular morphology of the endosteal surface caused point-contacts andconcentrated loads between these devices and cortical bone. Initialimplant fixation was achieved by interference fit at these points ofcontact.

High concentrated loads and stress-shielding between point-contacts cancause resorption of bone and implant loosening. Long-term implantfixation is dependent on cancellous bone growth around the surface ofthe implant where it is not contacting the endosteal surface of corticalbone.

Cements are commonly used to fill the void between the endosteal surfaceof cortical bone and the implant. Though commonly used, cements cancause adverse tissue reactions and complicate the load characteristicsof the bone-implant interface by adding a third material with its uniquematerial properties. Uncemented devices are being introduced for hip andknee prostheses. Some of these devices are contoured or require theendosteal surface of the cortical bone to be machined to increase theimplant-to-cortical bone surface area. Contouring the device surfaceincreases its cost and may require patient imaging and bone shaping.Machining bone removes healthy tissue and weakens the structuralstrength of the organ. Additionally, local heating of bone duringmachining can cause its death.

Hand-tool reaming, press-fit installation and cementing require skill.These procedures are sources of surgical variance and potentialprostheses failure. The combined issues of device design, device-boneinterface failure, micromotion, stress-concentration, stress-shieldingmaterial property differences and surgical variance limit the usefullifetime of many prostheses to 5 to 20 years.

The present invention addresses these problems in the prior art andprovides devices having coordinated self-seeking conforming members,where a known relationship exists between the pressure exerted on thesurrounding material and the mechanism engagement torque or force, andhaving the ability to contour to an irregular defect.

SUMMARY OF THE INVENTION

The present invention provides fasteners having coordinated self-seekingconforming members for conforming to a cavity. An actuator mechanismcoordinates and translates applied force for the independent ordependent movement of each member. The process of conforming also alignsthe fastener, and thereby aligns that which is attached to the fastener.The present fasteners are useful wherever implants are desired, andwherever aligning is needed. In particular, the fasteners are useful forhard tissue implants for humans and animals, such as cartilage and boneimplants; for anchoring prostheses; and for aligning devices as inindustrial technology.

An embodiment of the present invention provides a fastener forimplanting into a cavity, the fastener comprising a body; a plurality ofmembers movably connected to the body, each member being independentlymovable for coordinated self-seeking conforming to the cavity; and anactuator mechanism for coordinating and translating applied force toeach member.

As used herein, a “fastener” may also be referred to as an implant; a“cavity” is an enclosed space for receiving and holding a structure andmay be a hole, tube, cylinder, well, hard tissue defect, or the like. A“hard tissue defect” is a defect in bone or cartilage that may have beenconstructed surgically, by accident, or from disease. “Independentlymovable for coordinated self-seeking conforming to a cavity” means thateach member responds to applied force in a coordinated manner until itengages a wall of the cavity and a second member may continue to moveuntil it also engages a wall of the cavity. “Coordinated” means that allmembers move initially in response to applied force. “Self-seeking”means that a member moves in response to an applied force until itengages a wall of the cavity for independent movement. “Conforming”means that a member engages a wall of the cavity. “Movably connected”means directly or indirectly connected. A member may be a lever, afinger, a projection, a protrusion, a wing, a shoe, or an ear, or thelike.

In a preferred embodiment, an interfacial pressure exists between eachmember and the cavity when in use. In an even more preferred embodimentwhere the cavity is a hard tissue defect, a sufficient interfacialpressure exists between each member and the cavity to cause hard tissuedensity, in particular, bone density, to increase when in use.

The actuator mechanism may further comprise a locking mechanism forlocking the actuator mechanism. The locking mechanism may be selectedfrom the group consisting of a cap, a jam nut, a taper, a transversepin, a key, a spline, an abutment, and the like.

Where the cavity is a hard tissue defect, the fastener as describedherein may further comprise a prosthesis connected to the fastener. Theprosthesis may be a hard tissue trauma fixation device or hardwareselected from the group consisting of a dental implant, a spinalprosthesis, an intermedullary rod, a knee prosthesis, a shoulderprosthesis, a finger prosthesis, a hip prosthesis, a temporal-mandibularjoint, a dental implant with prosthetic tooth, a plate, a port, and thelike.

A further embodiment of the present invention includes a fastener asdescribed herein having a first member and a second member and whereinthe actuator mechanism comprises a journal; and a first link and asecond link, each link rotatingly and slidingly joined to the journal,the first link rotatingly joined to the first member and the second linkrotatingly joined to the second member such that when the journal ismoved, the first link and the second link move and cause the firstmember and the second member to move independently to conform to thecavity. The actuator mechanism may further comprise a bearing having abore for housing the journal, the journal further having an end movablyconnected to the bearing so that when the bearing is moved, the journalmoves through the bore of the bearing.

The invention includes a fastener as described herein having a firstmember and a second member and wherein the actuator mechanism comprisesa journal; and a cam slidingly and rotatingly connected to the journal,the cam further slidingly and rotatingly joined to the first member andto the second member such that when the journal is moved, the cam movesand causes the first member and the second member to move independentlyto conform to the cavity. The actuator mechanism may further comprise abearing having a bore for housing the journal, the journal furtherhaving an end movably connected to the bearing so that when the bearingis moved, the journal moves through the bore of the bearing.

Another embodiment is a fastener as herein described having a firstmember and a second member and wherein the actuator mechanism comprisesa journal; a first link having a first end and a second end, the firstend pivotally connected to the journal; a second link having a first endand a second end, the first end pivotally connected to the second end ofthe first link, and the second end pivotally connected to the firstmember; and a third link having a first end and a second end, the firstend pivotally connected to the second end of the first link, and thesecond end pivotally connected to the second member, wherein when thejournal is moved, the first link moves and acts on the second link andthe third link to cause the first member and the second member to moveindependently to conform to the cavity. The actuator mechanism mayfurther comprise a bearing having a bore for housing the journal, thejournal further having an end movably connected to the bearing so thatwhen the bearing is moved, the journal moves through the bore of thebearing.

A further fastener of the present invention as herein described has afirst member and a second member and wherein the actuator mechanismcomprises a journal; a first link having a first end and a second end,the first end pivotally and slidingly connected to the journal, and thesecond end pivotally connected to the first member; and a second linkhaving a first end and a second end, the first end pivotally andslidingly connected to the journal, and the second end pivotallyconnected to the second member; wherein when the journal is moved, thefirst link and the second link move to cause the first member and thesecond member to move independently to conform to the cavity. Theactuator mechanism may further comprise a bearing having a bore forhousing the journal, the journal further having an end movably connectedto the bearing so that when the bearing is moved, the journal movesthrough the bore of the bearing.

The fastener as herein described having a first member and a secondmember is an aspect of the invention wherein the actuator mechanismcomprises a journal; and a cam having a first slot and a second slot,the first slot slidingly and pivotally connected to the journal, and thesecond slot slidingly and pivotally joined to the first member and tothe second member such that when the journal is moved, the cam moves andcauses the first member and the second member to move independently toconform to the cavity. The actuator mechanism may further comprise abearing having a bore for housing the journal, the journal furtherhaving an end movably connected to the bearing so that when the bearingis moved, the journal moves through the bore of the bearing.

The fastener as herein described having a first member and a secondmember, each member having an arm, is an aspect of the invention,wherein the actuator mechanism comprises a shaft having a first end anda second end, and a component constrained to be in slidable contact withthe second end of the shaft and in contact with the arm of each membersuch that when the shaft is moved, the component moves in contact withthe arms and causes the first member and the second member to moveindependently to conform to the cavity. In a preferred embodiment, theshaft decreases in diameter at the second end.

A further aspect of the invention is a fastener as described hereinhaving a first member and a second member, each member having an angledsurface, and wherein the single actuator mechanism comprises a shafthaving a first end and a second end; and a component constrained by theangled surface of each member to be in slidable contact with the secondend of the shaft such that when the shaft is moved, the component movesin contact with the members and causes the first member and the secondmember to move independently to conform to the cavity. In thisembodiment, each member is movably limited by the body such that thecomponent is contained within the body by the angled surface of eachmember. In a preferred embodiment, the shaft decreases in diameter atthe second end.

A further embodiment of the invention is a fastener for implanting intoa cavity, the fastener comprising a body comprising a movable structure;a plurality of members rotatingly connected to the movable structure,each member being independently movable with respect to the body forcoordinated self-seeking conforming to the cavity; and an actuatormechanism within the movable structure for coordinating and translatingapplied force to conform independently each member to the cavity, theactuator mechanism comprising a journal rotatingly and slidinglyconnected to each member such that when the journal is moved through thebore of the body, each member moves symmetrically with respect to themovable structure and moves independently with respect to the body toconform to the cavity.

An embodiment of the invention is a fastener for implanting into acavity, the fastener comprising a body; a plurality of members movablyconnected to the body, each member being dependently movable forcoordinated self-seeking conforming to the cavity; and an actuatormechanism for coordinating and translating applied force to each member.“Dependently movable” means that the members move at the same time, whenone member engages a wall of the cavity, a second member is not able tomove further. For dependent movement, “self-seeking” means that movementof members is determined by a first member engaging a wall of thecavity. Further members do not continue to move.

A further embodiment is a fastener having dependent movement as hereindescribed having a first member and a second member and wherein theactuator mechanism comprises a journal rotatingly and slidingly joinedto the first member and to the second member such that when the journalis moved, the first member and the second member move dependently toconform to the cavity.

A further fastener having dependent movement has a first member and asecond member and wherein the actuator mechanism comprises a journal; afirst link having a first end and a second end, the first end pivotallyconnected to the journal, and the second end pivotally connected to thefirst member; and a second link having a first end and a second end, thefirst end pivotally connected to the journal, and the second endpivotally connected to the second member; wherein when the journal ismoved, the first link and the second link move to cause the first memberand the second member to move dependently to conform to the cavity.

A further fastener having dependent movement has a first member and asecond member, each member having an arm, wherein the actuator mechanismcomprises a shaft having a first end and a second end, the second endbeing in slidable contact with the arm of each member such that when theshaft is moved, the first member and the second member move dependentlyto conform to the cavity.

A further fastener having dependent movement has a first member and asecond member, each member having an angled surface, and wherein theactuator mechanism comprises a shaft having a first end and a secondend, the second end being in slidable contact with the angled surface ofeach member such that when the shaft is moved, the first member and thesecond member move dependently to conform to the cavity.

In each of the fastener embodiments having dependent movement, theactuator mechanism may further comprise a bearing having a bore forhousing the journal, the journal further having an end movably connectedto the bearing so that when the bearing is moved, the journal movesthrough the bore of the bearing.

A further embodiment of the invention is a fastener for securing astructure to a cavity where the structure is configured to fit to anouter surface of the cavity. The fastener comprises a body having afirst bore and a slot opening onto the first bore; a cylinder within thefirst bore, the cylinder having a driving mechanism; a member within theslot, the member movably connected to the body and acted on by thedriving mechanism for conforming to the cavity; and wherein when a forceis applied to the cylinder, the driving mechanism causes the member tomove to conform to the cavity, thereby securing the structure to thecavity. The driving mechanism may comprise an actuator, the member maycomprise a lobe, and in this case, the actuator meshes with the lobe ofthe member. In a preferred embodiment, the driving mechanism comprises aworm gear, the member comprises a plurality of gear teeth, and the wormgear meshes with the gear teeth of the member. The fastener may furthercomprise a locking means for locking the cylinder within the bore. Thelocking means may be selected from the group consisting of a retainer ora jam nut. The structure may be a prosthesis and may be selected fromthe group of prostheses described herein.

Materials suitable for fabrication of a fastener of the presentinvention may be a material that is at least biocompatible for thelength of intended use, and has sufficient structural strength. Abiocompatible material is selected from the group consisting of a metal,a ceramic, a polymer, and a combination thereof. Where the fastener isformed of a metal, the metal is titanium, titanium alloy, stainlesssteel, chromium cobalt, chromium cobalt alloy, or the like. Where thefastener is formed of a ceramic, the ceramic is silica glass, alumina,calcium phosphate, calcium carbonate, or the like. Where the fastener isformed of a polymer, the polymer is delrin, nylon, polyester,polymethylmethacrylate, polyethylene, or the like.

Use of the fasteners of the present invention for implanting into acavity and aligning the fastener within the cavity is an aspect of theinvention. The use comprises placing the fastener into the cavity andapplying force to conform each member of the plurality of members to thecavity thereby aligning the fastener with the cavity. The cavity may berelated to industry, or a hard tissue defect such as a bone or cartilagedefect.

Use of the fasteners of the present invention, where the cavity is ahard tissue defect of an animal, for fastening a prosthesis to the hardtissue defect is an aspect of the invention. The use comprises placingthe fastener into the hard tissue defect of the animal; applying forceto conform each member of the plurality of members to the cavity; andattaching the prosthesis to the fastener. Preferably, the animal is ahuman. In a preferred embodiment, a sufficient interfacial pressureexists between each member and the cavity to cause hard tissue densityto increase when in use.

Use of the fasteners of the present invention for fastening airplaneskin at a cavity site is an aspect of the present invention. The usecomprises placing the fastener into a cavity of airplane skin; andapplying force to conform each member of the plurality of members to thecavity thereby fastening the airplane skin.

Use of the fasteners of the present invention for aligning a part to anobject in automated production is a further aspect of the presentinvention. The use comprises placing the fastener onto the part; andapplying force to the fastener to conform each member of the pluralityof members to align the part to the object. In a preferred embodiment,the object is a robot or part thereof.

Several significant advantages are achieved by the present invention.The fasteners of the present invention, when implanted in bone tissue,for example, provide unique and novel designs that minimize micromotion,optimize the stress distribution to bone, allow material propertymatching through active mechanisms, assist in centering the device,present forces to the bone to stimulate it to become more dense,minimize or eliminate surgical variance and allow it to be tightened, ifloose. Applied force to the fastener may be from a tool attached to thefastener. The tool may push on the actuator mechanism to cause themembers to move.

The efficiency of the fastening device of the present invention isimproved considerably by the provision of its design and its operationalcompatibility with bone. Further advantages include independent movementof the expansion members for certain embodiments, conformation of theimplant-to-bone defect, application of a known bone-to-implantinterfacial pressure, capability to reengage or disengage the mechanismto refasten or remove the implant, drawing of the implant into thedefect by the action of the expansion components, compression of smallirregularities along walls of the hole or defect by the expandingcomponents to increase contact area, high implant surface area againstthe surrounding material, control of implant alignment or centeringwithin the defect, and firm initial fixation. All of these advantagesare accomplished without bending any implant component. This minimizesthe likelihood of component failure through residual stress in thedevice and fatigue loading. These advantages are significant whencompared to press-fit, screw thread and uniformly expanding fasteners.

Following long-standing patent law convention, the terms “a” and “an”mean “one or more” when used in this application, including the claims.

BRIEF DESCRIPTION OF THE DRAWINGS

Further objects and advantages of this invention will become apparentfrom consideration of the drawings and ensuing description of thepreferred embodiments.

FIG. 1a and FIG. 1b are cross-sectional plane views of a fastener havinga linkage-member mechanism in bone and configured as a bone contactingdental implant.

FIG. 2 is a cross-sectional plane view of a fastener having acammed-member mechanism configured and shown as a femoral component of ahip prosthesis.

FIG. 3 is a cross-sectional plane view of a fastener having athree-linkage mechanism configured as the mandibular component of atemporal-mandibular joint.

FIG. 4 is a cross-sectional plane view of a fastener with scissoringmembers and a two slot cam mechanism.

FIG. 5 is a cross-sectional plane view of a fastener with scissoringmembers, and sphere and shaft actuator mechanism configured as abone-contacting dental implant with prosthetic tooth.

FIG. 6a and FIG. 6b provide a cross-sectional plane view of a fastenerwith pinned members, and sphere and shaft actuator mechanism configuredas a dental implant. The dental implant is shown in bone with in-phase(FIG. 6b) and out-of-phase (FIG. 6a) member expansion.

FIG. 7a and FIG. 7b provide a cross-sectional plane view of a fastenerwith a member mechanism in a spherical rotating housing configured in aplate that allows rotation. The plate is held to the bone surface by thefastener.

FIG. 8a and FIG. 8b provide a cross-sectional plane view of a fastenerhaving a conformal mechanism including members with worm gears andpinions. A cross-sectional plane view magnified to illustrate themember's worm gear and pinion is shown in FIG. 8b.

FIG. 9a and FIG. 9b provide mechanical drawings of the implant fastenerused in Example 1. FIG. 9a shows the fastener ready for insertion in anextraction site. FIG. 9b shows the implant with its members partiallyengaged and operating out-of-phase from one another.

FIG. 10 shows the implant fasteners of the present invention reduced toa simplified model having the following parameters: A, Torque; B,Actuator (Power Screw); C, Cam; D, Fixed Axis of Rotation; E, Members;α1, Index member; α2, Reference Member; β, Cam angle.

FIG. 11 provides an equation for calculating interfacial pressure.

FIG. 12 provides a graph of torque to pressure multiplier (Z) versusmember orientation; reference member angle (deg) (Y), and index memberangle (deg) (X).

FIG. 13 provides a plot of pressure vs. torque as a function of pressuremultiplier: a, 10 Ncm; b, 20 Ncm; c, 32 Ncm; d, 300 mm Hg; □, maximummultiplier; ▪, minimum multiplier.

FIG. 14 provides a plot of the force versus displacement curve for thefastener of Example 1 with the members disengaged (closed). Maximumstrength—13.75 lb. Total energy—1.76 in-lb.

FIG. 15 provides a plot of the force versus displacement curve for thefastener of Example 1 with the members 75% engaged (¾ open). Maximumstrength—34 lb. Total energy—12.21 in-lb.

FIG. 16 provides a plot of the force versus displacement curve for theNobelpharma endosseous 20 mm×3.5 mm screw thread implant. Two tests wereperformed to determine repeatability of the method. Maximum strength—28lb. Total energy—0.66 in-lb.

FIG. 17 provides a histogram of combined maximum strength (hatchedbar,\\\\\\) and total energy (hatched bar, //////) for different designsand configurations of the fastener of the present invention as comparedto the Nobelpharma implant: 1 a and 1 b, Example 1 fastener, Member ¾Open; 2 a and 2 b, Example 1 fastener, Member Closed; 3 a and 3 b,Nobelpharma implant.

FIG. 18 provides results from dual subtraction radiographs of a memberfastener showing filling of the extraction site void between the membersand below the implant and an increase in bone density adjacent to themembers due to forces exerted by the members on the surrounding bone.Increases in bone mineral density is seen in light regions and decreasesin dark regions.

FIG. 19 provides a photograph of the member implant fastener specimenshowing dense bone adjacent to the foot of the members.

FIG. 20 shows a fastener embodiment configured as a dental implant.Starting from left is the fastener with one member closed and the secondpartially open demonstrating independent action of the members. Theabutment and screw are shown separately above and to the right of thefastener. At center left is the fastener with abutment attached. Themembers are fully expanded and opened equally. At center right is thefastener with the members together and at an angle to the body showingthe ability of the members to adapt to angled defects. The healing capis attached and a separate healing cap and screw are shown above and tothe right. At the far right is a fully expanded fastener with prosthetichuman tooth.

FIG. 21 shows a fastener configured as a femoral neck compressionfastener and plate. Starting at the upper right is the plate compressionand fixation screw, below it are the plate and an embodiment of theexpanding conformal component. Below and adjacent to the dog femur isthe assembled femoral compression system.

FIG. 22 shows a cross-sectional plane view of a fastener similar to thatof FIG. 1 configured for dependent movement of its members. The firstlink and second link 20 of FIG. 1 have been removed to convert theactuator mechanism to dependent movement.

FIG. 23 shows a cross-sectional plane view of a fastener including anactuator mechanism using two links running in an actuator slot to allowcoordinated self-seeking independent expansion of its members.

FIG. 24 shows a cross-sectional plane view of the fastener of FIG. 23where the slot has been changed to be a press-fit pin thus allowing thecoordinated self-seeking dependent expansion of its members.

FIG. 25 shows a cross-sectional plane view of a fastener where thesphere 420 of FIG. 5 has been removed; in the present embodiment, themembers are movable in a coordinated self-seeking dependent fashion.

FIG. 26 shows a cross-sectional plane view of a fastener as shown inFIG. 3 modified such that the member orientation with respect to theactuator is reversed so as to allow the members to swing out from thetop of the body.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

In a preferred embodiment, the present invention provides a fasteningmethod and device for bone so designed as to impart a considerablyimproved efficiency under substantially all attachment conditions. Anunderstanding of the orthopaedic problem; bone biology, physiology, andanatomy; and mechanical engineering and materials science have led tothe development of novel devices that are nonobvious because of thediverse technical experience required to combine this knowledge into asolution to this long studied and difficult medical problem.

Studies of bone biology and physiology have demonstrated the sensitivityof bone cells to mechanical loads. Excessive loads cause tissue deathand resorption, modest loads cause increases in density and strength asdescribed by Wolf's Law, while physiologically low skeletal loads causebone resorption, porosity and weakening (as in microgravity-inducedosteoporosis). Orthopaedic practice commonly requires fasteners for usein regular (drill hole) or irregular shaped (fracture) bone defects.Prior art technology is suboptimal with breakage and loosening a commonproblem.

In the present invention, material properties of static and fatiguestrength, biocompatibility and toxicity have been combined with themechanical requirements of the fastener to complement the physiology andbiology of bone and meet the general needs of orthopaedic medicine forprostheses and implants that are located on, within or through bone orcartilage.

The fastener allows controlled expansion of its members, the adaptationof components of the device to the surrounding tissue, and the abilityto determine the bone-to-implant interfacial pressure. Implant expansionis driven by the surgeon. The expanding components, most commonlyconsisting of pinned rotating members, may operate independently ordependently. Once expanding components are contacting bone, theinstallation force or torque can be used to compute the bone-to-implantinterfacial pressure.

The mechanical load exerted by the members on the margins of the bonedefect is such that the force applied by the members is within a rangethat will not fracture bone or cause it to deteriorate, and issufficiently great so as to firmly fasten the structure and stimulatebone to become more dense.

Several embodiments of the actuator mechanism are provided herein andare intended not to limit the device design but to broaden its scope byincluding examples of mechanisms with means to facilitate the presentinvention. In particular, a bearing is an optional aspect of thefasteners of the present invention. Different actuator mechanisms allowfor either independent or dependent movement of members, as describedherein.

Fastener Having a Linkage-Member Actuator Mechanism: An embodiment ofthe fastener of the present invention (FIG. 1a, FIG. 1b) includes anassembly having a single internal actuator mechanism including a bearing(01) with internally threaded bore, an externally threaded journal (10)having a transverse slot adjacent to one end, and two links (20) thatwhen joined with pins (30) to the slot in the journal (10) and members(60) and constrained to rotate about a second pin (40) within a lowerbody (50) together are capable of causing members (60) to moveindependently of one another so as to engage, conform, press upon, andbe retractable from, surrounding material. The bearing (01) isconstrained within the upper body (70) and lower body (50) so as tocontain the mechanism and resist fixation forces applied to the members(60).

The embodiment of FIG. 1a and FIG. 1b is shown in a drilled hole in amandible with gingival tissue (90), compact bone (92) and cancerous bone(94) surrounding the implanted fastener. In a drilled hole the members(60) expand equally to contact the surrounding compact bone. In a toothextraction site where the defect is irregular in its shape, the members(60) operate independently and conform to the defect as shown in FIG.1b.

In the operation of the present embodiment, when the bearing (01) is“tightened” by rotating about its central axis within the bore of thelower housing (50), the journal (10) is forced to move out of the boreof the bearing (01). Translation of the journal (10) causes the linkages(20) to cause the members to rotate about pin (40) and engage thesurrounding bone (92). If one of the members (60) contacts surroundingbone (92) then the linkages (20) begin to slide and rotate about pin(30) thus allowing the member (60) which was not in contact with bone(92) to continue its rotation about pin (40) until it conforms to andcontacts bone (92). Once both members (60) contact bone (92) thenadditional rotation of the bearing (01) loads the journal (10) causing apredictable force to be applied by the members (60) to the surroundingbone (92).

Fastener Having a Cammed-Member Actuator Mechanism: A further embodimentof the actuator mechanism (FIG. 2) is shown configured as a femoralprosthesis placed in the medullary compartment of the femur (194). Themechanism includes a bearing (100) having an internally threaded bore,externally threaded journal (110) having a journal pin (115) near oneend, and a cam with slot (120) that together are capable of causing eachof two members (130) to move independently of one another so as toengage, conform and press upon and, if disengaged, retract fromsurrounding cancellous bone (190) or cortical bone (192).

This embodiment uses an upper housing (140) and lower housing (150) tocontain the bearing (100) and support the movement of the members (130).The members (130) are pivotally connected to the lower half of thehousing (150) with pins (160) and to the cam (120) with a second set ofpins (170). The cam (120) is further connected to the journal (110) by ajournal pin (1 15).

This embodiment is combined with a femoral ball (106) and carrier (102)to complete the prosthesis. To ensure security of the mechanism a jamnut (180) is provided to lock the mechanism so as to prevent rotation ofthe bearing (100).

In the operation of the present embodiment, when the bearing (100) is“tightened,” the journal (110) is forced to move out of the bore of thebearing (100). The cam (120) is linearly moved by its pin (115)connection with the journal (110) causing the members (130) to berotated about the pivotal connections (160) with the housing (150). Whena first member (130) contacts a contour of the bone tissue cavity in itsrotation, the cam (120) tilts and slides to allow continued rotation ofthe second member (130) as well as continued linear movement of thejournal (110). Once both members (130) contact the contours of the bonetissue cavity, additional downward force on the journal (110) isbalanced by the resistive force caused by contact of the bone (192). Ameans of locking the mechanism can be achieved by a cap (180) that isfixed to the housing to contact and resist the rotation of the bearing(100).

Fastener Having a Three-Linkage Actuator Mechanism: A further embodimentof a fastener of the present invention uses an internal mechanismconsisting of a bearing (200), which can be locked by a removable cap(280), externally threaded journal (210), and three linkages (220, 223and 226) to operate the members (FIG. 3).

This embodiment uses a housing to contain the mechanism and support themovement of the conforming portion of the device. In this embodiment thehousing includes an upper (240) and lower half (250) with members (230)pivotally connected to the lower half of the housing (250) with pins(260).

The upper (240) and lower (250) housing have a bore. In this bore abearing (200) with an internally threaded bore engages an externallythreaded journal (210) which is pivotally coupled to one of the linkages(220) with a pin (263). This linkage is pivotally coupled with a pin(266) to each of two linkages (223 and 226) which are pivotally coupledat their second end to each of the members (230) with pins (270).Translation of the journal (210) causes independent expansion of themembers (230).

In the operation of the present embodiment, when the bearing (200) is“tightened,” the journal (210) is forced to move out of the bore of thebearing (200) causing the linkage (220) that is pivotally connected tothe journal to move. The translational and rotational movement of thislinkage (220) causes the other two linkages (223 and 226) to move.Movement of the three linkages (220, 223 and 226) together cause themembers (230) to move independently into the surrounding tissue.

Fastener having Journal-Double Linkage Actuator Mechanism: In FIG. 23 isshown an upper body (1240), lower body (1250), journal or actuator(1210), cap (1280), member (1230), links (1223 and 1226), and pins(1260), (1265) and (1270). The actuator pin (1265) is slidingly androtatingly connected to links (1223 and 1226). This embodiment issimilar to that of FIG. 3, however, it is more simply made and isconfigured for independent self-seeking movement of the members (1230).When in use, the bearing (1200) is turned, forcing actuator (1210) outof its bore which causes actuator pin (1265) to rotatingly slide in theactuator slot causing links (1226) and (1223) to act on members (1230)so as to cause them to rotate about pin (1260).

Fastener Having a Two-Slot Cam Actuator Mechanism: A further fastenershown in FIG. 4 uses a housing to contain the mechanism and support themovement of the conforming portion of the device. As with the otherembodiments, the housing consists of an upper (340) and lower half (350)with members (330) pivotally connected to the lower half of the housing(350) with a single pin (360) that is centrally located.

The upper housing (340) and lower housing (350) have a bore. In thisbore a bearing (300) with an internally threaded bore engages anexternally threaded journal (310) which is coupled to a cam (320) havinga plurality of slots with a pin (313) that is further coupled to each ofthe members (330) with pins (370). The cam (320) shows a differentconfiguration than previous embodiments having a pivotal slidingconnection to the journal pin (313) and a second pivotal slidingconnection to the two members (330) with pins (370). This cam (320)configuration is applicable to other embodiments and in contrast to thepreferred first and second embodiments the common pivot pin (360) of themember provides greater initial leverage in its unexpandedconfiguration.

In the operation of the present embodiment, when the bearing (300) is“tightened,” the journal (310) is forced to move out of the bore of thebearing (300). The cam (320) is linearly moved by its connection withthe journal (310) and the members (330) are rotated outward about thepivotal connection (360) with the housing (350). When one member (330)contacts a contour of the bone tissue cavity in its rotation, the cam(320) tilts to allow continued rotation of the other member (330) aswell as continued linear movement of the journal (310). Once bothmembers (330) contact the contours of the bone tissue cavity, additionaldownward force applied by the journal (310) is balanced by the resistiveforce of the bone tissue contacts.

Fastener Having a Sphere-Shaft Actuator Mechanism with ScissoringMembers: A further embodiment shown in FIG. 5 uses a sphere (420) toactuate members (430). This embodiment uses a one-piece housing (440) tocontain the mechanism and support the movement of the conforming portionof the device. This housing has members (430) pivotally connected with asingle pin (460) that is centrally located in the housing (440).

The housing (440) has a bore with internal threads over a portion of itslength and an internal taper that expands to the level of the pin (460)which is the pivot connection between the members (430) and the housing(440). In this bore an externally threaded shaft (400) engages theinternal threads. This shaft (400) contacts a sphere (420) that isconstrained by the housing (440) and the upper arms (410) of the members(430). This sphere (420) rides between the upper arms (410) of themembers (430). The shaft (400), sphere (420) and members (430) acttogether to independently expand the two members (430) from thecenterline of the housing (440). The shaft (400) can be replaced with anunthreaded member and used in a housing (440) with an unthreaded boreallowing an implant holding instrument to push on this member andtranslate the ball (420). An abutment (470) locks the shaft (400) andprovides a support for cement (490) and prosthetic tooth (480).

In the operation of the present embodiment, when the shaft (400) isturned, the sphere (420) is forced to move out of the bore of thehousing (440). The force on the sphere (420) is transferred through thearms (410) of the members (430) to produce rotation of the members (430)about the central pin (460). When one member (430) contacts a contour ofthe bone tissue cavity in its rotation, the sphere (420) slides on thestationary arm (410) as it continues rotation of the noncontactingmember (430). Once both members (430) contact the contours of the bonetissue cavity, additional downward force applied by the shaft (400) isbalanced by the resistive force of the bone tissue contacts.

Fastener Having a Sphere-Shaft Actuator Mechanism with Pinned Members: A20 further embodiment shown in FIGS. 6a and 6 b uses a sphere (510) tocause two members (530) to swing away from the housing (540). Thisembodiment uses a one piece housing (540) to contain the mechanism andsupport the movement of the conforming portion of the device. Thishousing has members (530) each pivotally connected with pins (560).

The housing (540) has a bore with internal threads. In this bore anexternally threaded shaft (500) engages the internal threads. This shaft(500) contacts a sphere (510) that is constrained by the opposing facesof the members (530). This sphere (510) rides between members (530). Theshaft (500), sphere (510) and members (530) act together toindependently expand the two members (530) from the centerline of thehousing (540).

An abutment (570) locks the shaft (500) and provides a support forcement (590) and prosthetic tooth (580). The implant is shown in a toothextraction site surrounded with gingival tissue (592), compact bone(594) and cancellous bone (596).

In the operation of the present embodiment, when the shaft (500) isturned, the sphere (510) is forced to move out of the bore of thehousing (540). The force on the sphere (510) is transferred through thesphere (510) to the members (530) to produce rotation of the members(530) about the pins (560). When one member (530) contacts a contour ofthe bone tissue cavity in its rotation, the sphere (510) slides on thestationary member (530) as it continues rotation of the noncontactingmember (530). Once both members (530) contact the contours of the bonetissue cavity, additional downward force applied by the shaft (500) isbalanced by the resistive force of the bone tissue contacts. Therotation of the members (530) is limited by contact between the housing(540) and members (530). This range is limited so that the sphere (510)cannot be pushed past the members (530) and out of the mechanism.

Fastener with Mechanism in a Spherical Rotating Housing Configured in aStructure: A further fastener shown in FIGS. 7a 7 b can be used tosecure a structure, for example a bone plate (650), to the surface of abone (692). This embodiment uses a spherical body (620) having twomembers (630). The spherical body (620) is pivotally connected withinthe plate (650) with a cap (640) having a bore with a spherical internalsurface which supports the movement of the members (630). Together themovement of the members (630) and the pivoting of the sphere (620)between the plate (650) and cap (640) allows the members (630) toindependently conform to a body cavity.

The spherical body (620) has a bore. Within this bore is a bearing (600)with an internally threaded bore. This bearing (600) is held within thebore of the sphere (620) with a locknut (680) having a bore. In the boreof the bearing (600) an externally threaded journal (610) engages theinternal threads. This journal (610) is pivotally and slidinglyconnected to members (630) with pins (670). The members (630) arepivotally connected to the spherical body (620) with pins (660) and acttogether to symmetrically expand from the centerline in relationship tothe spherical body (620). The rotation of the spherical body (620)combined with the symmetrical expansion of the members (630) withrespect to the spherical body (620) allows independent expansion of themembers (630) with respect to the plate (650) and conformation to thebone (692).

In the operation of the present embodiment, when the bearing (600) isturned, the journal (610) is forced to move out of the bore of thespherical body (620). The movement of the journal (610) causes themembers (630) to rotate about pins (660). When one member (630) contactsa contour of the bone tissue cavity in its rotation, the spherical body(620) rotates in the plate (650) to allow the noncontacting member (630)to continue to move. Once both members (630) contact the contours of thebone tissue cavity, additional downward force applied by the journal(610) is balanced by the resistive force of the bone tissue contacts.

Fastener with Worm Gear and Pinion Mechanism Configured in a Structure:A further embodiment shown in FIGS. 8a 8 b can be used to secure a body(700), for example, a plate, port or other structure having a bore(740), to the surface of a bone (780). This embodiment uses a gearedmechanism consisting of a drive cylinder (710) having a worm gear,member (730) having gear teeth (720), locking nut (750), member pin(760) and retainer (770). Two or more geared mechanisms can be used witha body (700).

The members (730) are pivotally connected to the body (700) with pins(760). The geared teeth (720) of the members (730) protrude intoseparate bores cut through the body (700) at its periphery. A drivecylinder (710) is located in each bore allowing a worm gear cut on thedrive cylinder (710) to mesh with the gear teeth (720) of the members(730). The drive cylinder is retained and locked into the bore withretainer (770) and locknut (750). The ability to actuate each memberindependently allows the members (730) of the implant to conform to abody cavity and hold the port (700) in place. In the design of thisembodiment the separate drive cylinders (710) can be replaced by acommon drive cylinder so as to rotate each member (730) simultaneously.

In the operation of the present embodiment, prior to placing the locknut(750), when the drive cylinder (710) is turned, the worm gear drives thegear teeth (720) and causes the member (730) to rotate. When one member(730) contacts a contour of the bone tissue cavity in its rotation thenoncontacting members (730) can be actuated to rotate using the drivecylinder. Once both members (730) contact the contours of the bonetissue cavity, additional rotational torque applied by the drivecylinder (710) is balanced by the resistive force of the bone tissuecontacts. Once engaged the locknut (750) is placed to stop any furtherrotation of the drive cylinder (710) or member (730).

Fastener having Journal-Member Actuator Mechanism for Dependent Movementof Members: In FIG. 22 is shown an upper body (1070), lower body (1050),journal or actuator (1010), jam nut (1001), member (1060), and pins(1030) and (1040). This embodiment is similar to that of FIG. 1,however, it is configured for dependent movement of the members (1060).When the actuator (1010) is pushed through the lower body (1050), pins(1030) slidingly rotate in the actuator (1010) slot causing members(1060) to precess about pin (1040) in a dependent and symmetricalmanner.

Fastener having Journal-Double Linkage Actuator Mechanism for DependentMovement of Members: In FIG. 24, the fastener of FIG. 23 has beenmodified to provide upper body (2240), lower body (2250), and a jam nut(2200) threadedly engaged with upper body (2240) and lockable by a cap(2280). The fastener shown in FIG. 24 has also been modified to changethe journal or actuator slot to a pin hole to receive pin (2265). Thiscauses a rotational connection between links (2223) and (2226), eachconnected by a pin (2270) to a member (2230) that causes dependentsymmetrical movement of members (2230) about pins (2260). When in use,actuator (2210) is pushed through the lower body (2250) causing theactuator pin (2265) to act on links (2226) and (2223) so as to causemembers (2230) to rotate about pin (2260).

Fastener having Shaft-Member Arm Actuator Mechanism for DependentMovement of Members: In FIG. 25, the fastener of FIG. 5 has beenreconfigured to include a housing (1440) supporting a shaft or actuator(1400). Abutment (1470) connects the fastener to prosthetic tooth (1480)with cement (1490). The fastener of FIG. 25 is adapted for dependentmovement of members (1430) about a pin (1460) by removing sphere (420)of FIG. 5, and reshaping arms (1410) at the point of sliding contactwith the actuator (1400).

Fastener having Members Movable from the Top rather than the Bottom ofthe Device: In FIG. 26, the fastener of FIG. 3 has been reconfigured toinclude an upper housing (3240), a lower housing (3250), a journal(3210) operably connected to a bearing (3200) disposed in upper housing(3240) and a locking cap (3280). Journal (3210) is connected to members(3230) by linkages (3220), (3223) and (3226) by pivot pins (3270).Members (3230) are mounted on lower housing (3250) by pivot pins (3260).The fastener of FIG. 26 is shown to demonstrate that any of thefasteners provided herein could be configured so that members (3230)pivot to swing out from the top instead of the bottom of the device.

A method of implanting a fastener of the present invention into a hardtissue defect includes the following steps: i) obtaining an animal inneed of a fastener of the present invention, ii) determining size of analready existing hard tissue defect, or constructing a hard tissuedefect and determining its size, iii) selecting a fastener having a sizeto fit in the defect and taking into account considerations of defectgeometry, whether the members will contact the walls of the defect orreach through the defect so as to extend into a cavity, and therelationship between interfacial pressure and actuation force and thestrength of the critical components, iv) placing the fastener into thehard tissue defect, v) applying force to the fastener using a tool thatapplies force sufficient to secure the device and stimulate bone tobecome more dense. The method may optionally include vi) placing ahealing cap over the fastener, or placing a prosthesis onto thefastener.

A method for determining interfacial pressure exerted on bonesurrounding an implanted fastener of the present invention includes thesteps of: i) applying force to the implanted fastener using a tool wherethe force can be measured, ii) measuring the extent of journaltranslation, iii) measuring index member angle, iv) measuring referencemember angle, v) determining interfacial pressure from the equationprovided in FIG. 11 for the device of FIG. 2. Similar equations can bederived for the other mechanism configurations in light of the teachingsof the present disclosure. In the case of dependent movement, the indexand reference member angles are equal.

Fasteners of the present invention may be machined and assembled by oneof skill in the art in light of the teachings of the present disclosure.Methods of use of a fastener of the present invention are also known toone of skill in the art in light of the teachings of the presentdisclosure.

Even though the invention has been described with a certain degree ofparticularity, it is evident that many alternatives, modifications, andvariations will be apparent to those skilled in the art in light of theforegoing disclosure. Accordingly, it is intended that all suchalternatives, modifications, and variations which fall within the spiritand the scope of the invention be embraced by the defined claims.

The following example is included to demonstrate a preferred embodimentof the invention. It should be appreciated by those of skill in the artthat the techniques disclosed in the example represent techniquesdiscovered by the inventor to function well in the practice of theinvention, and thus can be considered to constitute preferred modes forits practice. However, those of skill in the art should, in light of thepresent disclosure, appreciate that many changes can be made in thespecific embodiments which are disclosed and still obtain a like orsimilar result without departing from the spirit and scope of theinvention.

Example 1 In vivo Dental Implant Fastener and Evaluation Thereof

The present example provides an evaluation of an endosseous (bonecontacting) dental implant of the present invention. Devices weredesigned to be placed through the gingiva into a tooth extraction site,expand, conform to the defect and become immediately stable.

The design used the cammed linkage system to independently expand a pairof members (FIG. 9a, FIG. 9b and FIG. 2; the reference numerals for FIG.9a are: 810, healing cap; 820, actuator nut; 830, upper body; 840,actuator mandrel; 850, lower body; 860, actuator-cam pin; 870, cam; 880,member). The design used two cylinders that are press-fit together tohold the bearing and journal, and to form the body of the fastener. Twopinned members rotate about two tabs that protrude from the lower faceof the body. The members are pinned with the journal in the cam slot,allowing the journal and member pins to slide independently. The upperend of the journal is threaded into the actuator bearing. Rotation ofthe bearing by applying force to the installation instrument causes thejournal to move downward and engage the members through the cam. Thefasteners may further include a healing cap driver, an actuator driver,or anti-rotation spanner.

The methods used to evaluate the fasteners of the present inventionaddressed three broad topics: engineering design, engineeringevaluation, and in vivo and explant evaluation.

Engineering design for the cammed-member mechanism involved thedetermination of the appropriate size and shape for the experimentalanimal, its range of member motion and expansion, its extent ofout-of-phase member operation, component interference, the strength ofits critical components, a method to lock the mechanism, and itsbone-implant interfacial pressure as a function of mechanism engagementtorque.

Requirements for size, shape and extent of expansion of both implantdesigns were determined through the evaluation of fresh dog mandiblesprovided through the experimental surgery teaching program at theUniversity of Texas Health Science Center, (San Antonio, Tex.).Mandibles were cut in the mesial-distal and buccal-lingual planes. Themesial root of the first molar was selected as the first site forinvestigation. This selection provided size and shape information forimplant design. The strength characteristic of the necropsy specimensprovided an estimate of the extent of expansion required for the twoimplant designs.

The extent of member motion, out-of-phase operation and expansion forthe cammed-member implant required the detailed design of allcomponents. The body size and shape, mechanism's pin diameters, cam slotand overall length, member arm length, actuator-translation distance,and actuator-nut rotation versus translation relationship all effect theoperation of the mechanism.

A computer design simulation for the member implant was developed usingMATHCAD™ to account for and understand the large number of designvariables. This simulation allows the selection of all design variables,solved a system of equations, computed the operational range of themechanism, and provided a graphical layout of the mechanism to check forcomponent interference. This simulation allows rapid design assessmentof operational parameters and is well suited to support the resizing andoptimization of the member implant system.

Critical mechanism component strength was performed using conventionalmachine design theory. The critical components were determined to be theactuator-cam pin, actuator journal bearing and nut, and cam (FIG. 9a,FIG. 9b, and FIG. 2).

Actuator-cam pin: The standard method of determining the maximum forcesupportable by a clevis-pin arrangement as found in the present implantfasteners is the double lap shear equation (Shigley, J. E., MechanicalEngineering Design, 3rd ed., Holman, J. P., ed., McGraw-Hill Book Co.,1977).

Given values of 60 k psi maximum shear CTi-64) and a pin cross-sectionalarea of 1.26×10⁻³ in², the calculated maximum force the pin will supportbefore shear yielding occurs is 150.8 lb. A safety factor of 2 should beapplied, reducing the maximum expected sustainable load to 75.4 lb. Thisequates to 8.22 in-lb of torque applied to the actuator (Table 1).

A second, more conservative method of analysis is to consider the pin asa beam with constrained ends and a point load applied at the center. Forsuch a beam, the force required to initiate yielding is governed by thebending moment at the center of the pin radius and cross-sectionalgeometry. Using this method, maximum sustainable force is calculated tobe 55 lb. This equates to 5.99 in-lb of torque applied to the actuator(Table 1).

Actuator journal bearing: Failure of a power screw type actuator journalcan occur in one of two different manners, compression yielding of theentire screw or stripping of the threads. Thread recommendations assumethat the screw will fail just before the threads strip. The minimumthread engagement length necessary to prevent stripping of the threadsis assumed to be 0.07 in. When the members are deployed in theorientation of maximum screw travel, the remaining thread engagementlength is 0.1165 in. With a compressive yield strength of 120 k psi(Ti-64), the screw would be able to withstand a compressive load of 996lb. This equates to 109 in-lb of torque applied to the actuator (Table1).

Cam: The upper section of the cam with a thickness of 0.035 inches wasmodeled as a simply supported beam with a moment applied at each end.For such a beam, the force required to initiate yielding is governed bythe moment produced at the center of the beam, ½ the height of the beamand the second moment of inertia. For the upper and weaker section ofthe CAM, the maximum sustainable force is calculated to be 52.8 lb. Thisequates to 5.75 in-lb of torque applied to the bearing. The lowersection of the cam with a thickness of 0.06 inches was modeled as asimply supported beam. The maximum sustainable force for the lower beamis calculated to be 114 lb. This equates to 12.41 in-lb of torqueapplied to the bearing (Table 1).

TABLE 1 Maximum sustainable forces for critical components. ComponentMaximum Force (lb) Cam Upper Beam 52.8 Lower Beam 114.0 Bearing andjournal 996.0 Actuator-cam pin Double Lap Shear Method 75.4 Beam Method55.0

Using the beam method, the cam pin, and the upper portion of the cam canbe considered the critical members and equivalent, given the assumptionsused for the analysis. A sustainable force of 52.8 lb equates to 5.75in-lb of torque applied to the journal. The Vident IMPAC torque wrenchchosen to tighten the member implant fastener can deliver a maximum of2.83 in-lb (32 Ncm) of torque. This allows a safety factor of 2.0 forthe mechanism.

Mechanism locking and bacterial sealing is accomplished throughinterference of the healing cap 810, 280 or prosthesis abutment 470, 570and the actuator nut 820. The cap 810, 280 or abutment 470, 570, wheninstalled, jam against the actuator nut 820 causing it to bind againstthe internal aspects of the mechanism body. This creates threemetal-to-metal bacterial seals. One is between the cap and the body, asecond between the actuator nut and the internal face of the cap, andthe third between the lip of the actuator nut and the internal lip ofthe body. These three seal faces minimize the likelihood of bacterialmigration through the implant mechanism.

Bone-implant interfacial pressure is a function of the torque applied tothe bearing nut during the placement of the implant (FIG. 10). Thepressure applied to the implant-bone interface can be determined byexamination of the mechanism. The design used in this study allowed theimplant members to rotate from −10° to 57.5° (positive is out andnegative is in towards the centerline). This mechanism allows themembers to operate independently and 37.5 degrees out-of-phase from oneanother. The interfacial pressure applied to the bone interface can bemeasured by relating the force applied by the power screw (bearing andjournal) to the cam and members.

In operation, turning the bearing applies a force to the cam which, inturn, causes the members to rotate outward. It is convenient for thepurpose of this analysis to treat this as two separate functions. Theactuator screw can be analyzed as a power screw turning against a loadand the cam and members as a simple three bar mechanism.

The position of the cam and second member are computed if the positionof one member is known. This known position is equivalent to bonecontact of one member while the journal is translated and the secondmember is still moving. The rotation of the cam (βCam-Angle), given arestrained-member angle (α-index), and extent of journal translation(ΔX) is computed as shown in FIG. 11. The analysis of the power screw isa straightforward application of the equation given in “MechanicalEngineering Design”, Shigley and Mischke, (as cited herein) and shown inFIG. 11, with known values particular to the present implant fasteners.Using simple geometric principals and an understanding of the forcesapplied to the members the interfacial pressure value can be obtained.

The equation of FIG. 11 has three degrees-of-freedom: torque, indexmember angle, and reference member angle. To generate thetorque-pressure multiplier surface, the reference member is sweptthrough its full range of motion, then the index member is advanced 1°and again the reference member is swept. This algorithm is continued forthe range of the index member. The result is the torque-pressuremultiplier surface shown in FIG. 12. A new surface is created for eachnew value of applied torque and each design (size) of the implant. Thesurface in FIG. 18 represents an applied torque of 1 in-lb.

From the graph of FIG. 18, the orientation corresponding to the maximum(index angle=0°, reference angle=16°) and minimum (index angle=34°,reference angle=55°) multiplying effect can be found. To calculate thepressure (psi) on the reference member, the multiplier value associatedwith a particular set of member angles is multiplied by the torqueapplied to the implant. Taking these minimum and maximumtorque-to-pressure multiplication values as boundaries and varying thetorque from 0 to 9 in-lb (implant hinge pins fail at 6 in-lb to 8.22in-lb), an envelope of implant interfacial pressure as a function oftorque can be plotted as shown in FIG. 13.

IMPAC torque wrench (Vident) values of 10, 20 and 32 Ncm and anoscillometric method blood pressure monitor cuff release pressure of 300mmHg are shown in FIG. 13 for reference. If the implant will fail at thejournal-cm pin at 8.22 in-lb applied torque, a safety factor of overthree exists for a bearing torque of 32 Ncm.

Instruments for manipulating the implant fastener included ananti-rotation wrench, a bearing driver, or a healing cap driver. Theanti-rotation wrench is a two-pin spanner. The pins of the spannerengage two holes on the upper face of the body of the implant. Thespanner can be fastened to the body of the implant with the healing capto facilitate handling of the implant during placement. The bearingdriver has a male toroid shaped end. This end fits the female socket inthe bearing. Rotation of the driver turns the bearing and operates themechanism. The healing cap driver is a toroid shaped socket driver usedto place and remove the healing cap.

Mechanical testing of the pull-out resistance of dental implants wasperformed for the cammed member, wire-cage and conventional Nobelpharmaimplant designs. The bone contacting portion of each of these implantdesigns was embedded in paraffin and pull-in tension to determine theintrinsic resistance of the implant to being pulled from bone. Thewirecage and cammed-member implants were tested in a dosed and expandedconfiguration. The Nobelpharma 3.5 mm×20 mm implant was selected forcomparison testing because it is the largest and most clinicallysuccessful endosseous implant on the market.

Instron model 1127 with a 1000 lb load cell and analog control systemwas used for these tests. The implant was tested in two configurations,with member closed and member ¾ open. The Nobelpharma implant was testedas delivered. Load lb)—deflection (in) curves demonstrated that morework (area under the curve) was required to remove the implant fastenersof the present invention in comparison to the Nobelpharma implant (FIG.14, FIG. 15, and FIG. 16).

The maximum value of the pull-out strength was taken from the graphs.The area under the force-displacement curves were measured. This area isa measure of the work (energy) required to extract the implant from wax.Work and pullout yield strength for the three different implants werecompared in a histogram given in FIG. 17.

All of the implant configurations produced comparable maximum strengthvalues (crosshatched bar). Conversely, the total energy (solid bar)required to completely remove the implant from the wax was significantlygreater in the systems of the present invention. This suggests that theimplant fasteners of the present invention perform with greatermechanical toughness, resisting pullout even after failure of theimplant-material interface has been initiated.

In vivo evaluations were performed under AAALAC Protocol #92077-11-01-B2by placing two implants into mandibular first molar extraction sites insix heartworm-free dogs following tooth extraction. Teeth were sectionedand extracted. Gingiva was closed around the implant leaving the healingcap exposed. Implant sites were swabbed with PERIDEX™ during the twiceweekly evaluation for implant mobility, gingival inflammation andbleeding.

Clinical and radiographic evaluations were performed pre- andimmediately post-implantation as well as at 2, 5, 8 and 12 weekspost-implantation and periodically for one year. Soft tissue adaptationto the device was documented photographically. Implant position and bonedensity and morphology were determined radiographically. Stability wasassessed subjectively. At the end of the 12-week period the mechanism ofthe cammed-member implant was actuated and found to be tight.

Quantitative digital radiographic image analysis was used to determinethe bony changes in and around the implant as described by Ruttimann etal. (“Automated estimation of lesion size”, SPIE, Application of OpticalInstrumentation in Medicine XIII 535:325-330, 1985). A stent was used tohold the x-ray calibration wedge and film. The stent had a calibrationwedge imbedded on the occlusal surface which was made of abone-simulating material which was 25 mm long, 10 mm high and had a rampof 0-5 mm thickness. The reference wedge was made from a bone-equivalentepoxy resin (Model 450 Bone, Radiation Measurements, Inc., Middleton,Wis.).

The processed radiographs were converted to digitized images in640×480×8 bits format with pixel size of 60 micrometers. Assessment ofthe alveolar bone changes were performed with a quantitative digitalx-ray image subtraction technique. On the monitor image of theradiograph, an area of interest (AOI) was drawn between the members ofthe cammed-member implant within the region of the wire cage andadjacent to the body of the implants with trackball driven mouse.

The images were then subtracted and compared to the calibration wedgewhich provided an estimate of the bone mass changes around the implantand in the apical defect between the members.

Morphometric measurements of the alveolar bone were made using the samestandardized radiographs that were made for the quantitative imageanalysis. Digitized radiographic images magnified eight-fold on thecomputer monitor with a pixel size of 60 micrometers were analyzed usingRADWORKS™ software for distance and area measurements (Dove, RADWORKS™,San Antonio, Tex.). The vertical alveolar bone change was measured fromimplant collar to the alveolar bone crest at the mesial and distalimplant sides. The area of the crestal bone change between the adjacentteeth and the implant was measured by outlining the crestal bone levelin the baseline radiograph and follow-up radiographs and calculating thearea difference between these outlines.

An oral photograph of an implanted fastener healing cap showed goodsoft-tissue approximation and closure at 8 weeks following implantplacement.

The results of this study demonstrated that increases in bone mineraldensity could be measured adjacent to and between the members at thepoint of interfacial pressure. On average, decreases in bone mineraldensity were noted at the crestal portion of the implant.

Measurements of changes in bone morphology and density of the bonesurrounding the member implant were made. Linear measurements of crestalbone height changes were taken relative to the top of the implant. Bonemineral density measurements were taken at the mesial and distal borderof the upper, mid and lower (at the member interface with bone) portionof the body and between the members at the apex of the extraction site.

The subtracted image showed increases in bone mineral density in lightregions and decreases in dark regions (FIG. 18). The members weredemonstrated to have increased bone mineral density adjacent to themembers and at the apex of the extraction site. This increase in bonedensity indicated that load applied by the mechanism was physiologic andstimulated bone to form with higher density and strength.

Explant and histologic evaluations were performed on three dogsterminated at 8 weeks post-implant placement and at one year. The leftand right sides of the mandibles were separated at the sinphysis andfixed in FORMALIN™ for four weeks. Prior to embedding, the mandibleswere sectioned in the mesial-distal plane to reveal the implant embeddedin bone.

Four principal assessments were made from gross and scanning electronmicroscope (SEM) examinations. First, the implant was stable in bone.Second, bone healed around and within the implant in the extraction sitedefect. Third, force exerted on the surrounding bone caused it to becomemore dense. Fourth, there was direct implant-to-bone contact (FIG. 19).

Clinical and radiographic evaluations performed over a period of oneyear showed excellent soft tissue healing and increases in bone mineraldensity in and around the implant. Subsequent histologic evaluationsconfirmed the biocompatibility of the devices and the ability of bone tosubstantially fill the extraction site defect and heal around theimplant.

In summary, the principal observations from this study were: 1) thedesigns were feasible for use in extraction sites and surgicallyprepared osseous defects; 2) small fastener mechanisms could be builtwith sufficient strength for application in bone; 3) the implants andinstruments supplemented conventional oral surgical practice and mayreduce the sensitivity of implant outcome to variation in technique; 4)soft-tissue healed around the crestal portion of the implants; 5) bonehealed throughout the defect and within the implant mechanism; 6) theimplants were biocompatible and stable in bone following placement andafter one year; 7) dual-subtraction techniques were sensitive to changesin bone mineral density adjacent to and within the mechanism of theimplants; and 8) the pressure exerted by the member implant increasedthe density of bone at the implant interface.

Example 2 Prosthetic Teeth

Development of the fastener of Example 1 led to the construction of aprosthetic tooth and its testing as a dental implant. The implantfastener structure, healing cap with screw, and abutment with screw havebeen built and evaluated. Prosthetic teeth have been formed and attachedto the structure using the abutment. This embodiment as a dental implantis shown in FIG. 20.

This embodiment is currently implanted in dogs. A nine-month follow-upexamination showed that bone surrounding the implant is increasing. Noneof the devices have failed and the prosthetic teeth are easily placedinto position.

Example 3 Applications to Orthopaedics

Further uses of the fasteners of the present invention apply toorthopaedics. A femoral neck compression fastener and plate have beenfabricated and are being evaluated in an animal model (FIG. 21). Theexpanding and conformal aspects of this system are expected to providesignificant benefit to patients with femoral neck fractures. Thesefractures often occur spontaneously in elderly osteoporotic patients.These patients have poor bone quality and conventional femoral neckcompression systems, which most often use course screw threads, pullloose due to the poor bone quality. Reports indicate that the failurerate of conventional compression systems is between 40% and 70% (Olerudet al., “Internal Fixation of Femoral Neck Fractures: Two MethodsCompared”, J. Bone Joint Surg [Br] 73-B: 169, 1991).

The implant fasteners of the present invention contrast withconventional technology in that the conformal and expanding portion ofthe subject invention provide an excellent interlock with bone and actto pull the fracture site together so as to facilitate compressionacross the fracture site and stimulate healing. An additional advantageis that the conformal features of the device minimize the effects ofsurgical technique with respect to the angle of the hole drilled that isrequired to be placed into the femoral neck and ball prior to insertionof the device.

Example 4 Applications to Industry

The fasteners of the present invention may be used as anchoring,centering, or aligning devices in areas of technologies needing suchanchoring, centering, or aligning, especially where such activity iswithin an irregular cavity, or where irregularities exist in an internalsurface. Such areas of technology include water and oil well technology,welding technology, aircraft applications and in automated production,for example.

Fasteners of the present invention may be used for centering, holdingand/or aligning various tubular or cylindrical elements for variouspurposes, such as end-finishing, attachment of other members of variousshapes and functions, or centering a holding or clamping mechanism withrespect to a tubular member. One problem in welding tubular memberstogether is getting the clamping and guiding structure in properposition for holding the parts while forming the weld, especially wherethe tubular member has a curved section. Fasteners of the presentinvention may be useful for aligning and holding such parts, or as ameans for guiding a welding unit, especially for automatic orsemiautomatic welding.

Alignment of a clamping or holding mechanism in a proper orientationwith respect to a plane end surface of a pipe or other tube is a furtheruse of fasteners of the present invention. Further, holding orsupporting a special apparatus for positioning, holding and/or weldingbrackets, arms, special connectors, and the like onto or near the endsof tubular members particularly where accurate positioning and precisionholding are essential is a use of the present invention.

Fasteners of the present invention are useful in oil field applicationsinvolving fishing tools, for example. In situations of broken ortwisted-off drill pipe in a well bore, the downhole pipe must berecovered or the well is lost. The fastening and aligning capabilitiesof the present fasteners allow the capture and withdrawal of thedownhole pipe from the well bore. The fastener would be fixed to the endof a wireline and lowered into the well bore to the level of the brokenend of the downhole pipe. The fastener members would be placed in thebore of the downhole pipe. Once engaged, the fastener would be expandedand would lock to the walls of the bore of the pipe, whilesimultaneously aligning the downhole pipe with the wireline. Thefastening and aligning allow a direct and secure pull by the wireline onthe downhole pipe so as to lift and allow recovery of the downhole pipe.

Fasteners of the present invention have further utility in aircraftapplications where two plates overlap and require joining. In today'sfleet of aircraft, mechanical fatigue is causing the riveted joints ofthe aircraft's aluminum skin to fail. The failure can be avoided byredrilling the rivet hole to remove any cracks and replacing the rivet.Reriveting of the skin can be difficult and expensive. The presentinvention provides a unique advantage for rejoining the skin panels.Once the old rivet is removed and the hole prepared, a fastener of thepresent invention can be inserted in the hole and expanded so as tocompress the overlapping aluminum skins and form a new and strong unionbetween the skins and airframe.

In a further use of the fasteners of the present invention, variouscomponents require aligning in automated production. These productionprocesses vary from assembly to part alignment while running through aconveyor system. In order for wheels, headlight buckets, and otherobjects to be placed on the frame or body of an automobile, for example,they must be retrieved from stock, held, transported and placed on theautomobile. These processes require an adaptive holding and aligningdevice. Fasteners of the present invention would automatically fasten toa wheel rim and align the rim with the arm of a robot used to place therim on the axle, for example. This holding and alignment would allow therobot to automatically know the orientation of the wheel so that itcould repeatedly place a wheel on an axle.

All of the devices and methods disclosed and claimed herein can be madeand executed without undue experimentation in light of the presentdisclosure. While the devices and methods of this invention have beendescribed in terms of preferred embodiments, it will be apparent tothose of skill in the art that variations may be applied to the device,methods and in the steps or in the sequence of steps of the methoddescribed herein without departing from the concept, spirit and scope ofthe invention. All similar substitutes and modifications apparent tothose skilled in the art are deemed to be within the spirit, scope andconcept of the invention as defined by the appended claims.

What is claimed is:
 1. A fastener for implanting into a cavity thefastener comprising: a body including a first bore formed therein; aplurality of nonbendable members movably connected to the body, eachmember being dependently movable for coordinated self-seeking conformingto the cavity; an actuator mechanism for coordinating and translatingapplied force to each member, wherein the actuator mechanism comprises ajournal disposed in said first bore in said body and joined to eachmember by linkage operable such that when the journal is moved, eachmember moves dependently to conform to the cavity; and a bearing memberdisposed in a second bore in said body and cooperable with said body foraxial movement in said second bore to move said journal and said membersrelative to said body to cause said members to conform to said cavity.2. A fastener for implanting into a cavity, the fastener comprising: abody; a first nonbendable member and a second nonbendable member movablyconnected to the body, each member being dependently movable forcoordinated self-seeking conforming to the cavity; and an actuatormechanism for coordinating and translating applied force to each memberwherein the actuator mechanism comprises a journal; a first link havinga first end and a second end, the first end pivotally connected to thejournal, and the second end pivotally connected to the first member; asecond link having a first end and a second end, the first end pivotallyconnected to the journal, and the second end pivotally connected to thesecond member; wherein when the journal is moved, the first link and thesecond link move to cause the first member and the second member to movedependently to conform to the cavity; and a member engaged with saidbody and said journal and movable relative to said body axially in abore in said body to cause said journal to effect movement of said firstand second links.
 3. A fastener for securing a structure to a cavity,the structure configured to fit to an outer surface of the cavity, thefastener comprising a body having a first bore and a slot opening ontothe first bore; a cylinder within the first bore, the cylinder having adriving mechanism comprising an actuator; a nonbendable member withinthe slot, the member a lobe movably connected to the body and to thedriving mechanism for conforming to the cavity; and wherein when a forceis applied to the cylinder, the driving mechanism causes the nonbendablemember to move to conform to the cavity, thereby securing the structureto the cavity.
 4. The fastener of claim 3 further comprising a lockingmeans for locking the cylinder within the bore.
 5. The fastener of claim3 wherein the structure is a prosthesis.
 6. The fastener of claim 1, 2,or 3 formed of a biocompatible material selected from the groupconsisting of a metal, a ceramic, a polymer, and a combination thereof.7. Use of the fastener of claim 1, 2, or 3 for implanting into a cavityand aligning the fastener within the cavity comprising placing thefastener into the cavity; and applying force to conform each member ofthe plurality of members to the cavity thereby aligning the fastenerwith the cavity.
 8. Use of the fastener of claim 1, 2, or 3 forfastening airplane skin at a cavity site, comprising placing thefastener into a cavity of airplane skin; and applying force to conformeach member of the plurality of members to the cavity thereby fasteningthe airplane skin.
 9. Use of the fastener of claim 1, 2, or 3 foraligning a part to an object in automated production, comprising placingthe fastener onto the part; and applying force to the fastener toconform each member of the plurality of members to align the part to theobject.
 10. The use of the fastener as set forth in claim 9 where theobject is a robot or part thereof.
 11. Use of the fastener of claim 1,2, or 3 wherein the cavity is a hard tissue defect of an animal, forfastening a prosthesis to the hard tissue defect comprising placing thefastener into the hard tissue defect of the animal; applying force toconform each member of the plurality of members to the cavity; andattaching the prosthesis to the fastener.
 12. Use of the fastener ofclaim 11 wherein a sufficient interfacial pressure exists between eachmember and the cavity to cause hard tissue density to increase when inuse.